EP1742284A1 - High power implantable battery with improved safety and method of manufacture - Google Patents
High power implantable battery with improved safety and method of manufacture Download PDFInfo
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- EP1742284A1 EP1742284A1 EP06020748A EP06020748A EP1742284A1 EP 1742284 A1 EP1742284 A1 EP 1742284A1 EP 06020748 A EP06020748 A EP 06020748A EP 06020748 A EP06020748 A EP 06020748A EP 1742284 A1 EP1742284 A1 EP 1742284A1
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Images
Classifications
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- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01M—PROCESSES OR MEANS, e.g. BATTERIES, FOR THE DIRECT CONVERSION OF CHEMICAL ENERGY INTO ELECTRICAL ENERGY
- H01M4/00—Electrodes
- H01M4/02—Electrodes composed of, or comprising, active material
- H01M4/36—Selection of substances as active materials, active masses, active liquids
- H01M4/38—Selection of substances as active materials, active masses, active liquids of elements or alloys
- H01M4/381—Alkaline or alkaline earth metals elements
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/372—Arrangements in connection with the implantation of stimulators
- A61N1/378—Electrical supply
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/38—Applying electric currents by contact electrodes alternating or intermittent currents for producing shock effects
- A61N1/39—Heart defibrillators
- A61N1/3975—Power supply
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01M—PROCESSES OR MEANS, e.g. BATTERIES, FOR THE DIRECT CONVERSION OF CHEMICAL ENERGY INTO ELECTRICAL ENERGY
- H01M6/00—Primary cells; Manufacture thereof
- H01M6/14—Cells with non-aqueous electrolyte
- H01M6/16—Cells with non-aqueous electrolyte with organic electrolyte
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/38—Applying electric currents by contact electrodes alternating or intermittent currents for producing shock effects
- A61N1/39—Heart defibrillators
- A61N1/3956—Implantable devices for applying electric shocks to the heart, e.g. for cardioversion
- A61N1/3962—Implantable devices for applying electric shocks to the heart, e.g. for cardioversion in combination with another heart therapy
- A61N1/39622—Pacing therapy
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- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01M—PROCESSES OR MEANS, e.g. BATTERIES, FOR THE DIRECT CONVERSION OF CHEMICAL ENERGY INTO ELECTRICAL ENERGY
- H01M4/00—Electrodes
- H01M4/02—Electrodes composed of, or comprising, active material
- H01M4/36—Selection of substances as active materials, active masses, active liquids
- H01M4/48—Selection of substances as active materials, active masses, active liquids of inorganic oxides or hydroxides
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- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01M—PROCESSES OR MEANS, e.g. BATTERIES, FOR THE DIRECT CONVERSION OF CHEMICAL ENERGY INTO ELECTRICAL ENERGY
- H01M6/00—Primary cells; Manufacture thereof
- H01M6/42—Grouping of primary cells into batteries
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- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y02—TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
- Y02E—REDUCTION OF GREENHOUSE GAS [GHG] EMISSIONS, RELATED TO ENERGY GENERATION, TRANSMISSION OR DISTRIBUTION
- Y02E60/00—Enabling technologies; Technologies with a potential or indirect contribution to GHG emissions mitigation
- Y02E60/10—Energy storage using batteries
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y02—TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
- Y02P—CLIMATE CHANGE MITIGATION TECHNOLOGIES IN THE PRODUCTION OR PROCESSING OF GOODS
- Y02P70/00—Climate change mitigation technologies in the production process for final industrial or consumer products
- Y02P70/50—Manufacturing or production processes characterised by the final manufactured product
Abstract
i) a first anode,
ii) a first terminal for connecting the first anode to a first external lead;
iii) a first electrolyte operatively associated with the first anode; and
b) a second high-rate electrochemical cell comprising:
i) a second anode;
ii) a second terminal for connecting the second anode to a second external lead;
v) a second electrolyte operatively associated with the second anode; and
c) a cathode electrically associated with the first electrolyte and the second electrolyte, wherein the first cell is connected in parallel to the second cell; and
d) at least one resistive load electrically connected between the first external lead and the second external lead; and wherein the first high-rate cell and the second high-rate cell has a combined anode and cathode surface area of up to 180 cm2 and between 130 cm2 and 180 cm2.
Description
- The present invention relates generally to a power source for an implantable medical device, and more particularly, the present invention relates to a dual cell power source for optimizing implantable medical device performance.
- A variety of different implantable medical devices (IMD) are available for therapeutic stimulation of the heart and are well known in the art. For example, implantable cardioverter-defibrillators (ICDs) are used to treat those patients suffering from ventricular fibrillation, a chaotic heart rhythm that can quickly result in death if not corrected. In operation, the ICD continuously monitors the electrical activity of a patient's heart, detects ventricular fibrillation, and in response to that detection, delivers appropriate shocks to restore normal heart rhythm. Similarly, an automatic implantable defibrillator (AID) is available for therapeutic stimulation of the heart. In operation, an AID device detects ventricular fibrillation and delivers a non-synchronous high-voltage pulse to the heart through widely spaced electrodes located outside of the heart, thus mimicking transthoratic defibrillation. Yet another example of a prior art cardioverter includes the pacemaker/cardioverter/defibrillator (PCD) disclosed, for example, in
U.S. Pat. No. 4,375,817 to Engle, et al. This device detects the onset of tachyarrhythmia and includes means to monitor or detect progression of the tachyarrhythmia so that progressively greater energy levels may be applied to the heart to interrupt a ventricular tachycardia or fibrillation. Numerous other, similar implantable medical devices, for example a programmable pacemaker, are further available. - Regardless of the exact construction and use, each of the above-described IMDs generally includes three primary components: a low-power control circuit, a high-power output circuit, and a power source. The control circuit monitors and determines various operating characteristics, such as, for example, rate, synchronization, pulse width and output voltage of heart stimulating pulses, as well as diagnostic functions such as monitoring the heart. Conversely, the high-power output circuit generates electrical stimulating pulses to be applied to the heart via one or more leads in response to signals from the control circuit.
- The power source provides power to both the low-power control circuit and the high-power output circuit. As a point of reference, the power source is typically required to provide 10-20 microamps to the control circuit and a higher current to the output circuit. Depending upon the particular IMD application, the high-power output circuit may require a stimulation energy of as little as 0.1 Joules for pacemakers to as much as 40 Joules for implantable defibrillators.
- Suitable power sources or batteries for IMD's are virtually always electrochemical in nature, commonly referred to as electrochemical cells. Acceptable electrochemical cells for IMDs typically include a case surrounding an anode, a separator, a cathode, and an electrolyte. The anode material is typically a lithium metal or, for rechargeable cells, a lithium ion containing body. Lithium batteries are generally regarded as acceptable power sources due in part to their high energy density and low self-discharge characteristics relative to other types of batteries. The cathode material is typically metal-based, such as silver vanadium oxide (SVO), manganese dioxide, etc.
- IMDs have several unique power source requirements. IMDs demand a power source with most of the following general characteristics: very high reliability, highest possible energy density (i.e., small size), extremely low self-discharge rating (i.e., long shelf life), very high current capability, high operating voltage, and be hermetic (i.e., no gas or liquid venting).
- These unique power source requirements pose varying battery design problems. For example, for the heart monitoring function of an AID, it is desirable to use the lowest possible voltage at which the circuits can operate reliably in order to conserve energy. This is typically in the order of 1.5 - 3.0 V. On the other hand, the output circuit works most efficiently with the highest possible battery voltage in order to produce firing voltages of up to about 750 V. Traditionally, all manufactured implantable cardioverter defibrillators used a battery system comprised of two cells in series to power the implantable device. This power source of approximately 6 volts provided improved energy efficiency of the output circuit at the expense of energy efficiency of the monitoring circuit. However, a two-cell battery was undesirable from a packaging, cost, and volumetric efficiency perspective.
- Eventually, improvements in output circuit design allowed the use of a single 3-volt cell while still maintaining good energy efficiency. Most ICDs are now designed with a single cell battery instead of dual cells connected in series. This approach was taken to improve the volumetric efficiency. In order to achieve the same power capability of the dual cell approach, the electrode surface area of the single cell must be at least equivalent to the total electrode surface area of the dual cell battery. However, the increased electrode surface area of a single cell poses a potential hazard to the IMD should an internal short circuit develop in the battery cell. If the electrode surface area is too high (approximately above 90 cm2 for a Li/SVO battery) and an internal short develops, the battery can get hot enough to potentially destroy the IMDs electronics and possibly burn the patient. As a result, most IMD and IMD battery manufacturers have adopted a design rule, which limits the surface area of a single cell to approximately 90 cm2. This is significantly less surface area than a typical dual cell design where the surface area was approximately 130 cm2. Hence, these single cell ICD batteries produced less power and the result was longer capacitor charge times. Many studies have proposed that defibrillation and cardioversion shocks are most effective when delivered as quickly as possible following detection of arrhythmia. The chance of terminating an arrhythmia in a patient decreases as the length of time it takes for therapy to be delivered to the patient increases. Therefore, the shorter the charge time for the capacitors the more effective the defibrillation therapy. Typically, battery electrode sizes are inversely proportional to the charging time. Therefore, the quicker the desired charging time, the larger the battery.
- While single battery systems have proved workable for implantable cardioverter defibrillators, the use of a single battery system necessarily involves a compromise between the ideal power supply and the hazards associated with large surface area electrodes. Accordingly, it would be desirable to provide for an improved dual battery power system for an implantable cardioverter defibrillator, which overcomes the problems of earlier attempts at dual battery systems.
Implantable medical devices may include one or more of the following features: (a) a hermetic enclosure, (b) a low-power control circuit located in the enclosure, (c) a high-power output circuit locate din the enclosure for delivering an electrical pulse therapy, (d) a power source and circuitry located in the enclosure for powering the low-power control circuit and the high-power output circuit, the power source and circuitry, (e) a first high-rate cell, (f) a second high-rate cell wherein the first cell and second cell are electrically connected in parallel to the low-power control circuit and the high-power output circuit, (g) at least one resistive load electrically connected between the first high-rate cell and the second high-rate cell, the at least one resistive load having a resistive value to prevent, in the event of an internal short in one of the high-rate cells, the shorted high-rate cell from substantially draining the other high-rate cell wherein either high rate cell is able to provide power for both the low-power control circuit and the high-power output circuit, in the event of a short in the other high-rate cell, and (h) a switching circuit electrically connected between the first high-rate cell and the second high-rate cell for selectively coupling the first high-rate cell to the second low-rate cell upon activation of the high-power output circuit. - The electrochemical battery of the invention includes the following features: (a) a first high-rate electrochemical cell comprising: a first anode which may include a first anode current collector, a first terminal for connecting the first anode to a first external lead, and a first electrolyte operatively associated with the first anode, (b) a second high-rate electrochemical cell comprising: a second anode which may include a second anode current collector; a second terminal for connecting the second anode or current collector to a second external lead; and a second electrolyte operatively associated with the second anode, (c) a cathode electrically associated with the first electrolyte and the second electrolyte, wherein the first cell is connected in parallel to the second cell; and (d) at least one resistive load electrically connected between the first external lead and the second external lead, and wherein the first high-rate cell and the second high-rate cell has a combined anode and cathode surface area of up to 180 cm2 and between 130 cm2 and 180 cm2. Of course, the cathode could be the external lead, or both anode and cathode could be connected to external leads.
- A method of manufacturing an electrochemical battery according to the present invention includes the following steps: (a) providing a first high-rate electrochemical cell, comprising the steps of: providing a first cathode which may include a first cathode current collector, connecting a first external lead to the first cathode or current collector, and activating the first high-rate cell with an electrolyte solution operatively associated with the first cathode,(b) providing a second high-rate electrochemical cell, comprising the step of: providing a second cathode which may include a second cathode current collector, connecting a second external lead to the second cathode or current collector, and activating the second electrochemical cell with the electrolyte solution operatively associated with the second cathode, (c) associating an anode electrically with the electrolyte in the first high-rate cell and the second high-rate cell, wherein the first cell is connected in parallel to the second cell, (d) connecting at least one resistive load electrically between the first external lead and the second external lead and wherein the first high-rate cell and the second high-rate cell has a combined anode and cathode surface area of up to 180 cm2 and between 130 cm2 and 180 cm2. The method may further comprise the step of (e) connecting the anode to a battery casing to provide a negative charge on the casing.
- Methods for manufacturing an implantable medical device may include one or more of the following steps; (a) providing a hermetic enclosure, (b) providing a low-power control circuit in the enclosure, (c) providing a high-power output circuit in the enclosure for delivering an electrical pulse therapy, (d) providing a power source and circuitry in the enclosure for powering the low-power control circuit and the high-power output circuit, (e) providing a first high-rate cell, (f) providing a second high-rate cell, (g) connecting the first cell and second cell electrically in parallel to the low-power control circuit and the high-power output circuit, (h) connecting at least one resistive load electrically between the first high-rate cell and the second high-rate cell, and (i) connecting a switching circuit electrically between the first high-rate cell and the second high-rate cell for selectively coupling the first high-rate cell to the second low-rate cell upon activation of the high-power output circuit.
- FIG. 1 is a simplified schematic view of one embodiment of an implantable medical device (IMD) incorporating a power source in accordance with the present invention;
- FIG. 2 is a simplified schematic circuit diagram of a power source in accordance with the present invention for use with the IMD of FIG: 1;
- FIG. 3 is a simplified schematic diagram of an embodiment for a power source in accordance with the present invention;
- FIG. 4 is a simplified schematic diagram of another embodiment for a power source in accordance with the present invention;
- FIG. 5 is a simplified schematic diagram of another embodiment for a power source in accordance with the present invention;
- FIG. 6 is a simplified schematic diagram of a high-rate dual-cell battery embodiment in accordance with the present invention;
- FIG. 7 is a simplified schematic diagram of another high-rate dual-cell battery embodiment in accordance with the present invention;
- FIG. 8 is a simplified schematic diagram of another high-rate dual-cell battery embodiment in accordance with the present invention.
- FIG. 9 is a simplified schematic diagram of another high-rate dual-cell battery embodiment in accordance with the present invention.
- The following detailed description is to be read with reference to the figures, in which like elements in different figures have like reference numerals. The figures, which are not necessarily to scale, depict selected embodiments and are not intended to limit the scope of the invention. Skilled artisans will recognize that the examples provided herein have many useful alternatives that fall within the scope of the invention.
- FIG. 1 is a simplified schematic view of one embodiment of an implantable medical device ("IMD") 20 in accordance with the present invention and its relationship to a
human heart 22. The IMD 20 is shown in FIG. 1 as preferably being a pacemaker/cardioverter/defibrillator (PCD), although the IMD may alternatively be a drug delivery device, a neurostimulator, or any other type of implantable device known in the art. The IMD includes a case orhermetic enclosure 23 and associatedelectrical leads enclosure case 23 contains various circuits and a power source. The leads 24, 26 and 28 are coupled to theIMD 20 by means of amulti-port connector block 30, which contains separate ports for each of the three leads 24, 26, and 28 illustrated. - In one embodiment, lead 24 is coupled to a
subcutaneous electrode 40, which is intended to be mounted subcutaneously in the region of the left chest. Alternatively, an active "can" may be employed such that stimulation is provided between an implanted electrode andenclosure case 23. In yet another embodiment, stimulation is provided between two electrodes carried on a single multipolar lead. - The
lead 26 is a coronary sinus lead employing an elongated coil electrode that is located in the coronary sinus and great vein region of theheart 22. The location of the electrode is illustrated in broken line format at 42, and extends around theheart 22 from a point within the opening of the coronary sinus to a point in the vicinity of the left atrial appendage. -
Lead 28 is provided with anelongated electrode coil 38, which is located in the right ventricle of theheart 22. Thelead 28 also includes ahelical stimulation electrode 44, which takes the form of an extendable/retractable helical coil, which is screwed into the myocardial tissue of the right ventricle. Thelead 28 may also include one or more additional electrodes for near and far field electrogram sensing. - In the system illustrated, cardiac pacing pulses are delivered between the
helical electrode 44 and thecoil electrode 38. Theelectrodes coil electrode 38 and theelectrode 40, and betweencoil electrode 38 andelectrode 42. During sequential pulse defibrillation, it is envisioned that pulses would be delivered sequentially betweensubcutaneous electrode 40 andcoil electrode 38, and between thecoronary sinus electrode 42 andcoil electrode 38. Single pulse, two electrode defibrillation pulse regimens may also be provided, typically betweencoil electrode 38 and thecoronary sinus electrode 42. Alternatively, single pulses may be delivered betweenelectrodes IMD 20 will depend somewhat on the specific single electrode pair defibrillation pulse regimen is believed more likely to be employed. - Regardless of the exact configuration and operation of the
IMD 20, theIMD 20 includes several basic components, illustrated in block form in FIG. 2. TheIMD 20 includes a high-power output circuit 50, a low-power control circuit 52, a power source 54 (shown with dashed lines), andcircuitry 56. As described in greater detail below, thepower source 54 is preferably a dual-cell configuration, and can assume a wide variety of forms. Similarly, thecircuitry 56 can include analog and/or digital circuits, can assume a variety of configurations, and electrically connects thepower source 54 to thehigh power circuit 50 and the low-power circuit 52. - The high-
power output circuit 50 and the low-power control circuit 52 are typically provided as part of an electronics module associated with theIMD 20. In general terms, the high-power output circuit 50 is configured to deliver an electrical pulse therapy, such as a defibrillation or a cardioversion/deribrillation pulse. In sum, the high-power output circuit 50 is responsible for applying stimulating pulse energy between the various electrodes 38-44 (FIG. 1) of theIMD 20. As is known in the art, the high-power output circuit 50 may be associated with a capacitor bank (not shown) for generating an appropriate output energy, for example in the range of 0.1-40 Joules. - The low-
power control circuit 52 is similarly well known in the art. In general terms, the low-power control circuit 52 monitors heart activity and signals activation of the high-power output circuit 50 for delivery of an appropriate stimulation therapy. Further, as known in the art, the low-power control circuit 52 may generate a preferred series of pulses from the high-power output circuit 50 as part of an overall therapy. - The
power source 54 and associatedcircuitry 56 can assume a wide variety of configurations, as described in the various embodiments below. Preferably, however, thepower source 54 includes a first, high-rate cell 60, and a second, high-rate cell 62. However, it is fully contemplated thatpower source 54 could contain a plurality of high-rate cells within volumetric reason so thatIMD 20 does not become to large for implantation or uncomfortable to the patient. Notably the first andsecond cells cells cells rate cells rate cells rate cells rate cells U.S. Pat. No. 5,439,760 to Howard et al. for "High Reliability Electrochemical Cell and Electrode Assembly Therefor" andU.S. Pat. No. 5,434,017 to Berkowitz et al. for "High Reliability Electrochemical Cell and Assembly Therefor," the disclosures of which are hereby incorporated by reference. High-rate cells U.S. Pat. Nos. 5,312,458 and5,250,373 to Muffuletto et al. for "Internal Electrode and Assembly Method for Electrochemical Cells;"U.S. Pat. No. 5,549,717 to Takeuchi et al. for "Method of Making Prismatic Cell;"U.S. Pat. No. 4,964,877 to Kiester et al. for "Nonaqueous Lithium Battery;" andU.S. Pat. No. 5,14,737 to Post et al. for "Electrochemical Cell With Improved Efficiency Serpentine Electrode;" the disclosures of which are herein incorporated by reference. - Materials for the cathode of high-
rate cells rate cells U.S. Pat Nos. 5,221,453 ;5,439,760 ; and5,306,581 to Crespi et al , although other types of SVO may be employed. It is to be understood that electrochemical systems other than those set forth explicitly above may also be utilized for high-rate cells - With the above-described parameters of high-
rate cell 60 and high-rate cell 62 in mind, one preferred combination of apower source 54A andcircuitry 56A is depicted schematically in FIG. 3. Thepower source 54A includes high-rate cell 60A and high-rate cell 62A as described above. UnlikeU.S. Pub. No. 2002/0183801 A1 herein incorporated in its entirety by reference, which includes a high-rate and low-rate cell selectively connected in parallel,circuitry 56A electrically connects high-rate cell 60A and high-rate cell 62A in parallel to high-power output circuit 50 and low-power control circuit 52. In particular, thecircuitry 56A includes aswitch 70 configured to selectively couple high-rate cells 60A and 62A to high-power control circuit 50. In this regard,circuitry 56A can include additional components/connections (not shown) for activating and deactivatingswitch 70 in response to operational conditions described below.Circuitry 56A further includesresistive load 64 to limit the current delivered from a non-shorted cell to a shorted cell in the event of an internal short within one ofcells 60A or 62A. - This battery circuit design allows two high-rate cells to be connected in parallel to achieve the same power capability as two cells connected in series.
Resistor 64 is selected such that R ≥ 10RCell where R is the resistance ofresistive load 64 and RCell is the resistance of high-rate cell power circuitry 52. Generally, R can be any reasonable value within the specifications above, but preferably R is between 10-100 ohms and RCell is approximately .5 ohm. This resistive relationship allows bothcells 60A and 62A to be discharged uniformly under pacing and sensing conditions, which is described in more detail below. - In normal operation, switch 70 is open until it is necessary to deliver a defibrillation pulse and then the switch is closed.
Switch 70 is selected such that RSwitch << R << R Charge, where RCharge is the input impedance of high-power circuitry 50.Switch 70 is closed only when charging a defibrillation capacitor (not shown) and would be enabled only when the voltage acrossload 64 was below a pre-determined value of approximately 20 millivolts indicating that neithercell 60A nor 62A has an internal short. Ifswitch 70 was enabled when eithercell 60A or 62A had an internal short, then the current from the non-shorted cell would dissipate into the shorted battery and would quickly deplete both cells, create enough heat to damage circuitry, and possibly cause discomfort the patient. In analternative embodiment load 64 could be substituted with a fuse. - This power source/circuitry configuration provides a distinct advantage over prior art, single-cell and dual-cell in series designs. The primary advantage is two high-rate cells can be assembled in parallel in the same enclosure. This is generally 20% more volumetrically efficient than two cells in series. Further, the risk of damage to the IMD and harm to the patient is substantially reduced. Another advantage of the present invention is that it allows single cell electronic circuits to be retrofitted to a parallel two-cell design with significantly minimal circuit design changes. During operation of the IMD 20 (FIG. 1), the
power source 54A is, from time-to-time, required to deliver a high-current pulse or charge to high-power output circuit 50 while maintaining a voltage high enough to continuously power low-power control circuit 52. If the supply voltage drops below a certain value, theIMD 20 will cease operation. This power source/circuitry configuration places the high-rate cells 60A and 62A in parallel to power both low-power control circuit 52 and when necessary high-power circuit 50. During a transient high power pulse, such as a defibrillation pulse, theswitch 70 is operated to couple high-rate cell 60A with high-rate cell 62A with minimal resistance and therefore substantially all the power fromcells 60A and 62A is transferred to high-power circuit 50. The low battery resistance provided by the parallel combination ofcells 60A and 62A prevents an excessive voltage drop during a transient high power pulse and assures continuous operation of low-power circuit 50. Further, where desired, thecells 60A and/or 62A can be sized and shaped to satisfy certain volumetric or shape constraints presented by the IMD 20 (FIG. 1). - With reference again to FIG. 3, if an internal short were to occur within either
cell 60A or 62A andresistive load 64 were not incircuit 56A, then cell 62A would begin to discharge intocell 60A until cell 62A was depleted beyond usefulness. This would makeIMD 20 unable to provide therapeutic stimulation and thusIMD 20 would have to be explanted and another IMD implanted. Further, the short would create a lot of heat, which could destroy the electronics of the IMD and cause potentially serious discomfort to the patient. However, withresistive load 64 betweencell 60A and 62 A incircuit 56A, cell 62A is limited in the amount of power that can be delivered to shortedcell 60A due to the parallel construction. - The parallel battery construction of the present invention allows
cells 60A and 62A to deplete at an equal rate over the life ofIMD 20. For example, when a defibrillation pulse is needed, switch 70 is closed, after it is determined that there is no internal short incells 60A or 62A, andcells 60A and 62A begin discharging into high-power circuit 50. The only difference in the current path betweencell 60A and 62A is that the current path for cell 62A must travel through the resistance ofswitch 70. It's of note that the current path is generally throughswitch 70 and notresistor 64 since current will take the path of least resistance. Therefore, since Rswitch has a lower value thanload 64, the current path from cell 62A will be throughswitch 70. Sinceswitch 70 has a small resistance,cell 60A and 62A will deplete at a substantially equal rate during defibrillation pulses since there is a minimal voltage drop atswitch 70. - In a similar fashion, when
cells 60A and 62A are powering low-power circuit 52 the only difference in the current path betweencell 60A and 62A is that the current path forcell 60A must travel throughload 64. Sinceload 64 has a relatively small resistance and the current traveling throughload 64 is between 10-20 microamps, then the voltage drop atload 64 is extremely low, approximately between 0.1 and 2 millivolts, and thereforecell 60A and 62A will deplete at a substantially equal rate while supplying low-power circuit 52. - With reference to FIG. 4, another embodiment for a power source is shown. The circuit is substantially the same as the circuit in FIG. 3, except that switches 68 and 66 have been added to
circuit 56B. The circuit of FIG. 4 allows for one ofcells 60B and 62B to become a backup should the other one experience an internal short. For example, normally switches 68 and 66 are closed to provide normal operation or the circuit andIMD 20. However, should a short be detected onload 64, switch 66 is opened. If current ceases to flow throughload 64, then it is determined that an internal short has occurred in high-rate cell 60B and switch 68 is opened and switch 66 is closed again to provide power toIMD 20. If current continues to flow throughload 64, then it is determined that an internal short has occurred in high-rate cell 62B and switch 66 remains closed. Since eachcell 60B and 62B is a high-rate cell,IMD 20 is able to function normally, except for a slower defibrillation capacitor-charging time, until cell 50B becomes depleted enough and explanting is necessary. One additional embodiment associated with FIG. 4. On rare occasion the failure of a circuit component can effectively short circuits the battery. The heat generated during this failure mode can cause significant discomfort to the patient. With the design shown in FIG. 4, an external short would also show up as a voltage drop acrossload 64. The same algorithm described forces one cell to effectively disconnect, thereby greatly reducing the rate of energy dissipation due to the short. - With reference to FIG. 5, another embodiment for a power source is shown. The circuit is similar to the circuit of FIG. 3 except that
switch 70 has been removed. This embodiment still protectsIMD 20 from an internal short, however, this embodiment is much more inefficient when operating in a defibrillating mode. This is because the current fromcell 60C must travel throughload 64. This creates a large voltage drop atload 64 and thus it takes longer to fully charge the defibrillation capacitor. - With reference to FIG. 6, a simplified schematic of a high-rate dual cell battery is shown. In this
embodiment power source 54 is shown havingbattery case 72,anode 74,cathode 76,cathode 77,separator 86,feedthrough 84,feedthrough 82,terminal 78, andterminal 80.Battery case 72 is shown in dotted lines, as the casing can be variable in shape and construction.Battery case 72 can be a deep drawn case as discussed inU.S. Pat. No. 6,040,082 (Haas et. al. ) herein incorporated in its entirety by reference or a shallow drawn case as discussed inU.S. patent application no. 10/260,629 attorney docket number P-10765.00 filed on September 30, 2002 titled Contoured Battery for Implantable Medical Devices and Method of Manufacture herein incorporated in its entirety by reference.Battery case 72 is preferably made of a medical grade titanium, however, it is contemplated thatbattery case 72 could be made of almost any type of material, such as aluminum and stainless steel, as long as the material is compatible with the battery's chemistry in order to prevent corrosion. Further, it is contemplated thatbattery case 72 could be manufactured from most any process including but not limited to machining, casting, thermoforming, or injection molding. - In the embodiment of FIG. 6, one
electrode 74 is continuous and is connected tocase 72. The alternate electrode is in twoseparate pieces piece electrical lead feedthroughs case 72. It is contempleated thatbattery 54 can be case negative (anode connected to case) or case positive (cathode connected to case). As shown,dual cell battery 54 has oneanode 74, which is utilized by afirst cell chamber 88 and asecond cell chamber 90, which are separated byseparator 86. There is no requirement of a hermetic seal betweencells Separator 86 is used to prevent direct electrical contact betweenanode 74 andcathodes separator 86 is not required for the present invention and can andpower source 54 can operate without it. Further, it is noted that the anode/cathode relationship could be reversed. For example,anode 74 could be replaced with a cathode as long ascathodes cells cell chamber Cathodes cells external leads battery case 72 throughfeedthroughs power source 54 is shown with two feedthroughs, it is fully contemplated thatbattery case 72 could have one feedthrough to accommodate bothleads resistive load 92 is shown connected between leads 78 and 80. As discussed above, load 92 functions to limit the amount of power delivered from a non-shorted cell to a shorted cell. With reference to FIG. 7, a simplified schematic of another high-rate dual cell battery is shown. In contrast to the dual cell embodiment of FIG. 6,continuous electrode 74 is not connected tocase 72. Insteadelectrical lead 79 extends throughfeedthrough 89 to makecase 72 neutral. - With reference to FIG 8, a simplified schematic of another high rate dual battery is shown. In contrast to the dual cell embodiment of FIG. 6, the anode is not continuous and each
piece case 72. This would be equivalent to taking two completely separte cells and placing them in the same battery case. - With reference to FIG. 9, a simplified schematic of another high rate dual battery is shown. This design is similar to the embodiment of FIG. 8, except electrical leads96 and 98 traverses through
feedthroughs 92 and 94 to make a case neutral design. If the battery shares electrolyte (or a common electrode), the cells do not directly short if one of the cells has an internal short because in order to have such an internal short, two conditions are required. First, there must be a direct electrical connection between an anode and a cathode. Second, there must be an ionic pathway between the electrically connected anode and cathode in order to have a complete circuit. In our examples, the second condition is present, but not the first. For the historical method of connecting two entirely separate cells in series, we have the first condition, but not the second. Thus, it would be impossible to place two cells in series in the same enclosure (with a common electrolyte) because both conditions are met and the cells would short. In a parallel configuration, however, it is possible to enclose them with the same electrolyte because there is no electrical pathway between the anode and cathode. - It will be appreciated that the present invention can take many forms and embodiments. The true essence and spirit of this invention are defined in the appended claims, and it is not intended that the embodiment of the invention presented herein should limit the scope thereof.
Claims (30)
- An electrochemical battery, comprising:a) a first high-rate electrochemical cell comprising:i) a first anode;ii) a first terminal for connecting the first anode to a first external lead;iii) a first electrolyte operatively associated with the first anode; andb) a second high-rate electrochemical cell comprising:i) a second anode;ii) a second terminal for connecting the second anode to a second external lead;v) a second electrolyte operatively associated with the second anode; andc) a cathode electrically associated with the first electrolyte and the second electrolyte, wherein the first cell is connected in parallel to the second cell; andd) at least one resistive load electrically connected between the first external lead and the second external lead; and wherein the first high-rate cell and the second high-rate cell has a combined anode and cathode surface area of up to 180 cm2 and between 130 cm2 and 180 cm2.
- An electrochemical battery of claim 1 wherein the first and second high-rate cells discharge at a generally equal rate.
- An electrochemical battery of claim 1 wherein the first high-rate cell and the second high-rate cell are housed in one casing.
- An electrochemical battery of claim 1 wherein the first electrolyte and the second electrolyte are the same electrolyte.
- An electrochemical battery of claim 1 wherein the at least one resistive load has a resistive value to reduce, in the event of an internal short in one of the high-rate cells, the rate at which the shorted high-rate cell drains the other high-rate cell.
- An electrochemical battery of claim 5 wherein either high rate cell is able to provide power for a circuit in the event of a short in the other high rate cell.
- An electrochemical battery of claim 5 wherein either high rate cell is able to provide power for a circuit in the event of a short in the other high rate cell.
- An electrochemical battery of claim 1, wherein the first terminal and the second terminal are the same.
- An implantable medical device comprising:a hermetic enclosure;a low-power control circuit located in the enclosure;a high-power output circuit located in the enclosure for delivering an electrical pulse therapy; anda power source and circuitry located in the enclosure for powering the low-power control circuit and the high-power output circuit, the power source and circuitry, said power source and circuitry further comprising the electrochemical battery of claim 1,wherein the first high-rate cell and second high-rate cell are electrically connected in parallel to the low-power control circuit and the high-power output circuit; and
at least one resistive load electrically connected between the first high-rate cell and the second high-rate cell, the at least one resistive load having a resistive value to limit, in the event that the first high-rate cell is internally shorted, the rate at which such internally shorted first high-rate cell drains the second high-rate cell. - An implantable medical device of claim 9, wherein the at least one resistive load value is between 10 ohms and 100 ohms.
- An implantable medical device of claim 9, wherein the first high-rate cell and the second high-rate cell has an electrode surface area up to 90 cm2 each.
- An implantable medical device of claim 11, wherein the electrode surface area is between 65 cm2 and 90 cm2.
- An implantable medical device of claim 9, wherein the first high-rate cell and the second high-rate cell are maintained within a single case.
- An implantable medical device of claim 9, wherein the first high-rate cell and the second high-rate cell include a cathode, and further wherein the first high-rate cell and the second high-rate cell share a common anode.
- An implantable medical device of claim 9, wherein the first high-rate cell and the second high-rate cell include an anode, and further wherein the first high-rate cell and the second high-rate cell share a common cathode.
- An implantable medical device of claim 15, wherein the cathode is selected from the group consisting of silver oxide, vanadium oxide, silver vanadium oxide, manganese dioxide, copper oxide, copper silver vanadium oxide, lead oxide, monofluoride, chromium oxide, bismuth-containing oxide, copper sulfate, and mixtures thereof.
- An implantable medical device of claim 16, wherein the anode of the first high-rate cell and the anode of the second high-rate cell are formed from lithium.
- An implantable medical device of claim 9, further comprising a switching circuit electrically connected between the first high-rate cell and the second high-rate cell for selectively coupling the first high-rate cell to the second low-rate cell upon activation of the high-power output circuit.
- A method for manufacturing an electrochemical battery comprising the steps of:a) providing a first high-rate electrochemical cell, comprising the steps of:i) providing a first cathode;ii) connecting a first external lead to the first cathode;iii) activating the first high-rate cell with an electrolyte solution operatively associated with the first cathode; andb) providing a second high-rate electrochemical cell, comprising the steps of:i) providing a second cathode;ii) connecting a second external lead to the second cathode;iii) activating the second electrochemical cell with the electrolyte solution operatively associated with the second cathode; andc) associating an anode electrically with the electrolyte in the first high-rate cell and the second high-rate cell, wherein the first cell is connected in parallel to the second cell; andd) connecting at least one resistive load electrically between the first external lead and the second external lead, wherein the first high-rate cell and the second high-rate cell has a combined anode and cathode surface are of up to 180 cm2 and between 130 cm2 and 180 cm2.
- The method of claim 19 wherein the first and second high-rate cells discharge at a generally equal rate.
- The method of claim 19 further comprising the steps of connecting electrically the anode to a battery casing to provide a negative charging on the casing.
- The method of claim 19 wherein the cathode of the first high-rate cell and the cathode of the second high-rate cell are selected from the group consisting of silver oxide, vanadium oxide, silver vanadium oxide, manganese dioxide, copper oxide, copper silver vanadium oxide, lead oxide, carbon monofluoride, chromium oxide, bismuth-containing oxide, copper sulfate, and mixtures thereof.
- The method of claim 10, wherein the anode is formed from lithium.
- A method for manufacturing an implantable medical device comprising the steps of claim 1 for manufacturing an electrochemical cell and further comprising the steps of:e) providing a hermetic enclosure;f) providing a low-power control circuit in the enclosure;g) providing a high-power output circuit in the enclosure for delivering an electrical pulse therapy; andh) providing a power source and circuitry in the enclosure for powering the low-power control circuit and the high-power output circuit; and further wherein said step c comprises the steps of:iii) connecting the first cell and second cell electrically in parallel to the low-power control circuit and the high-power output circuit; andiv) connecting at least one resistive load electrically between the first high-rate cell and the second high-rate cell.
- The method of claim 24, wherein the at least one resistive load has a resistive value to limit, in the event of an internal short in one of the high-rate cells, the rate at which the shorted high-rate cell drains the other high-rate cell.
- The method of claim 24, wherein the at least one resistive load value is between 10 ohms and 100 ohms.
- The method of claim 24, wherein the first high-rate cell and the second high-rate cell has an electrode surface area up to 90 cm2 each.
- The method of claim 27, wherein the electrode surface area is between 65 cm2 and 90 cm2.
- The method of claim 24, wherein the first high-rate cell and the second high-rate cell are maintained within a single case.
- The method of claim 24, further comprising the steps of connecting a switch circuit electrically between the first high-rate cell and the second high-rate cell for selectively coupling the first high-rate cell to the second low-rate cell upon activation of the high-power output circuit.
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EP04758748A EP1611630B1 (en) | 2003-03-31 | 2004-03-31 | High power implantable battery with improved safety and method of manufacture |
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Also Published As
Publication number | Publication date |
---|---|
JP2006523134A (en) | 2006-10-12 |
WO2004091021A1 (en) | 2004-10-21 |
DE602004018841D1 (en) | 2009-02-12 |
US20040193227A1 (en) | 2004-09-30 |
EP1995806A1 (en) | 2008-11-26 |
EP1746677A1 (en) | 2007-01-24 |
DE602004005975D1 (en) | 2007-05-31 |
CA2520780A1 (en) | 2004-10-21 |
EP1611630A1 (en) | 2006-01-04 |
DE602004018840D1 (en) | 2009-02-12 |
EP1742284B1 (en) | 2008-12-31 |
EP1746677B1 (en) | 2008-12-31 |
US7209784B2 (en) | 2007-04-24 |
DE602004005975T2 (en) | 2008-01-17 |
EP1611630B1 (en) | 2007-04-18 |
JP4916306B2 (en) | 2012-04-11 |
EP1995806B1 (en) | 2011-10-05 |
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